Transport of cells in hydrogels

ABSTRACT

The present invention relates to hydrogels which may be used to encapsulate or entrap live cells. The invention further relates to methods for transporting live cells which are encapsulated or entrapped within hydrogels from a first location to a second location. The invention further relates to method of treating a wound, disease or tissue injury, e.g. an ocular injury or a damaged ocular surface in a subject using a hydrogel comprising corneal stem cells. The hydrogels used in such methods may be ones which have been transported from a first location to a second location.

The present invention relates to hydrogels which may be used toencapsulate or entrap live cells. The invention further relates tomethods for transporting live cells which are encapsulated or entrappedwithin hydrogels from a first location to a second location and releaseof live cells upon reaching the second location. The invention furtherrelates to methods of treating a wound, disease or tissue injury, e.g.an ocular injury or a damaged ocular surface in a subject using ahydrogel comprising corneal stem cells. The hydrogels used in suchmethods may be ones which have been transported from a first location toa second location.

Although basic cell culture techniques have been used for over 100years, the development of the biotechnology industry and the more recentindustrialisation of these processes has produced a high demand for cellculture products. These products are needed both for biopharmaceuticalproduction and for laboratory-based research.

However, whilst cell culture consumables, for example, media, sera andassociated reagents, may readily be transported at room or ambienttemperatures, special conditions need to be applied to thetransportation of live cells in order to maintain cell viability.

Traditionally, live cells have generally been transported by one ofthree methods:

(i) Frozen, packed in dry ice. This can require up to 20 kg of dry icefor long journeys.

(ii) Refrigerated. This requires specialised equipment for refrigerationand hence increases distribution costs.

(iii) Cultures at ambient temperature. This requires shorttransportation times (i.e. of the order of minutes or hours) to avoidsignificant deterioration of the cell cultures.

It can readily be appreciated, therefore, that all three of the abovemethods have significant disadvantages.

The invention is based on the use of certain hydrogels. Some hydrogelshave previously been used for the storage of living tissues.

For example, EP 1 266 570 A1 relates to the preservation of livingorganism tissue by coating the tissue with a thermo-reversiblehydrogel-forming polymer. Examples of such polymers are given aspolypropylene oxide-polyethylene oxide copolymers and polyethylene oxidetriol polymers. With regard to other polymers, EP 1 266 570 states thatagar gels and alginic acid-type gels have a gel-sol temperature which istoo high for use with physiological tissues and that the enzymesrequired for gel-sol conversion of collagen gels damage living tissues.

JP 8023968A relates to the prevention of cultured skin from beingdamaged by vibration or inversion by placing the skin in a gelatin soland then lowering the temperature to convert the sol into gel therebyfixing the skin in the gelatin gel. The gelatin gel is said to providesupport for the cultured skin.

WO2010/069589 refers to the use of a homogenous mixture of agarose andagarase for covering or enveloping cells during cell transport. It isnoted (Example 2) that the covering or enveloping of cells in this waydid not significantly affect the rate of cell proliferation.

The current invention, however, is based, at least in part, upon therecognition that the encapsulation or entrapment of dispersed cellswithin certain hydrogels not only maintains the viability of the cellsencapsulated or entrapped therein, but that it actually suppresses celldivision and/or differentiation within those cells at temperatures whichinclude ambient temperature. The recognition of this fact thusfacilitates new uses for hydrogels, including the short- and medium-termstorage of cells within hydrogels to suppress cell division and/ordifferentiation, and the use of such hydrogels as carriers for cellsduring transportation of those cells, e.g. the sending of cells thoughthe post upon request. In particular, this recognition allows thetransportation of hydrogels comprising corneal cells from a donor to arecipient, and subsequent methods of treatment of ocular injuries ordamaged ocular surfaces in the recipient. Hydrogels comprising othercells types may be used for other treatments, e.g. as a wound dressing.

In particular, the invention demonstrates enhanced mechanical propertieswhich are associated with strontium alginate gels and gels which arereinforced (e.g. with nylon meshes), and improvements in the viabilityof cells which are immobilised within gels whose pore size has beencontrolled using a pore size controlling agent such as HEC. Cells mayreadily be released from such gels, thus facilitating further increasedviability rates.

In one aspect therefore, the invention provides a method fortransporting cells from a first location to a second location, themethod comprising the steps: (i) encapsulating or entrapping the cellsin a hydrogel, wherein the hydrogel is in the form of a thin layer ordisc; (ii) transporting the cell-containing hydrogel from the firstlocation to the second location; and optionally, (iii) releasing thecells from the hydrogel at the second location.

In a further aspect, the invention provides a method for preparing cellsfor transportation from a first location to a second location, themethod comprising the steps: (i) encapsulating or entrapping the cellsin a hydrogel, wherein the hydrogel is in the form of a thin layer ordisc; and (ii) packaging the cell-containing hydrogel for transportationfrom the first location to the second location.

In a further aspect, the invention provides a method for preparing cellsfor transportation from a first location to a second location, themethod comprising the steps: (i) encapsulating or entrapping the cellsin a hydrogel, wherein the hydrogel is in the form of a thin layer ordisc; (ii) packaging the cell-containing hydrogel; and optionally, (iii)dispatching the cell-containing hydrogel for transportation to thesecond location.

In yet a further aspect, the invention provides a method for fulfillingan order or request for cells, the method comprising the steps: (i)receiving an order or request for cells; (ii) encapsulating orentrapping the desired cells in a hydrogel, wherein the hydrogel is inthe form of a thin layer or disc; (iii) dispatching the cell-containinghydrogel for transportation to the location specified in the order orrequest; and optionally, (iv) transporting the cell-containing hydrogelto the location specified in the order or request.

In yet a further aspect, the invention provides the use of a hydrogel asa storage medium during the transportation of cells from a first to asecond location, wherein the hydrogel is in the form of a thin layer ordisc or sheet.

In certain aspects of the invention, there is provided a compositioncomprising a hydrogel wherein a population of cells is encapsulated orentrapped within the hydrogel.

In some embodiments, the composition is packaged in a form suitable fortransportation to a remote location.

In other aspects of the invention, there is provided a method oftreating an ocular injury in a subject, the method comprising the steps:(a) providing a hydrogel comprising corneal stem cells; (b) contactingthe ocular injury with said hydrogel; and optionally (c) securing thesaid hydrogel at the site of the ocular injury.

The hydrogel referred to herein comprises a hydrogel-forming polymerhaving a cross-linked or network structure or matrix; and aninterstitial liquid. The hydrogel is capable of suppressing orpreventing cell division and/or differentiation in cells encapsulated orentrapped therein. Preferably, the hydrogel is semi-permeable.

The term “hydrogel-forming polymer” refers to a polymer which is capableof forming a cross-linked or network structure or matrix underappropriate conditions, wherein an interstitial liquid and cells may beretained within such a structure or matrix. The hydrogel will compriseinternal pores.

Initiation of the formation of the cross-linked or network structure ormatrix may be by any suitable means, depending on the nature of thepolymer.

The polymer will in general be a hydrophilic polymer. It will be capableof swelling in an aqueous liquid. In one embodiment of the invention,the hydrogel-forming polymer is collagen. In this embodiment, thecollagen hydrogel comprises a matrix of collagen fibrils which form acontinuous scaffold around an interstitial liquid and the cells.Dissolved collagen may be induced to polymerise/aggregate by theaddition of dilute alkali to form a gelled network of cross-linkedcollagen fibrils. The gelled network of fibrils supports the originalvolume of the dissolved collagen fibres, retaining the interstitialliquid. General methods for the production of such collagen gels arewell known in the art (e.g. WO2006/003442, WO2007/060459 andWO2009/004351).

The collagen which is used in the collagen gel may be any fibril-formingcollagen. Examples of fibril-forming collagens are Types I, II, III, V,VI, IX and XI. The gel may comprise all one type of collagen or amixture of different types of collagen. Preferably, the gel comprises orconsists of Type I collagen. In some embodiments of the invention, thegel is formed exclusively or substantially from collagen fibrils, i.e.collagen fibrils are the only or substantially the only polymers in thegel. In other embodiments of the invention, the collagen gel mayadditionally comprise other naturally-occurring polymers, e.g. silk,fibronectin, elastin, chitin and/or cellulose. Generally, the amounts ofthe non-collagen naturally-occurring polymers will be less than 5%,preferably less than 4%, 3%, 2% or 1% of the gel (wt/wt). Similaramounts of non-natural polymers may also be present in the gel, e.g.polylactone, polylactide, polyglycone, polycaprolactone and/or phosphateglass.

In some embodiments of the invention, the hydrogel-forming polymer isalginic acid or a alginate salt of a metal ion. Preferably, the metal isa Group 1 metal (e.g. lithium, sodium, or potassium alginate) or a Group2 metal (e.g. magnesium, calcium, barium or strontium alginate).Preferably, the polymer is sodium alginate or calcium alginate orstrontium alginate, most preferably strontium alginate.

One factor which determines alginate gel permeability is the mannuronic(M) and guluronic (G) acid contents of the gel. Gels with a high M:Gratio have a small intrinsic pore size. The M:G ratio may be manipulatedto increase the permeability of gels as necessary to improve theviability of encapsulated cells. High M alginates are, however, morebiocompatible and clinically useful than high G alginates which tend toform very brittle and viscous gels. In some embodiments, the G contentof the alginate gel is 0-30%. In some embodiments, the M content ispreferably 30-70%. In some preferred embodiments, the gel is an alginategel with a M content of 50-70% or 60-70% and the gel additionallycomprises or comprised HEC.

In yet other embodiments of the invention, the hydrogel-forming polymeris a cross-linked acrylic acid-based (e.g. polyacrylamide) polymer.

In yet further embodiments, the hydrogel-forming polymer is across-linkable cellulose derivative, a hydroxyl ether polymer (e.g. apoloxamer), pectin or a natural gum.

In some embodiments of the invention, the hydrogel is notthermo-reversible at physiological temperatures, i.e. the sol-geltransition of the hydrogel cannot be obtained at a temperature of 0-40°C.

The structure of the hydrogel may be changed by varying theconcentration of the hydrogel-forming polymer in the hydrogel. Thestructure affects the viability of the cells in the hydrogel, the rateof differentiation of the cells as well as affecting the robustness ofthe gel and its handling properties.

Preferred concentrations of the hydrogel-forming polymer in the hydrogelare 0.2-2.6% (weight of polymer to volume of interstitial liquid),0.2-0.4%, 0.4-0.5%, 0.5-0.7%, 0.7-1.1%, 1.1-1.3%, 1.3-2.2% and 2.2-2.6%.

In other embodiments, the concentration of the hydrogel-forming polymerin the hydrogel is above 0.25%, 0.3%, 0.4%, 0.5% or 0.6%. In otherembodiments, the concentration of the hydrogel-forming polymer in thehydrogel is below 2.4%, 1.5%, 1.4%, 1.3% or 1.2%. In some preferredembodiments, the concentration of the hydrogel-forming polymer in thehydrogel is about 0.3%, about 0.6% or about 1.2%. In some particularlypreferred embodiments, the concentration of the hydrogel-forming polymerin the hydrogel is about 1.2%. In some particularly preferredembodiments of the invention, the hydrogel is formed from about 1.2%sodium alginate or from about 1.2% strontium alginate.

It is recognised that mammalian cells are of different sizes. Preferablythe pore size is optimised therefore for the type of cells which areentrapped within the hydrogel. In some embodiments of the invention, thehydrogel is obtained or obtainable using a pore size increasing agent.This agent may form an integral part of the hydrogel when in use, or itmay be completely, substantially completely or partially removed fromthe hydrogel prior to use. Preferably, the pore size increasing agent isan agent which produces pores in the range 0.1-3.0 μm, preferably0.2-3.0 μm, 0.1-1.0 μm or 0.1-0.4 μm.

The internal pore dimensions of the pores within the hydrogels may bemeasured by chemically dehydrating the hydrogel, exposing the internalsurfaces, coating them with gold and then viewing them using a scanningelectron microscope.

In some embodiments, the pore size increasing agent is an agent which issoluble in the interstitial liquid and which dissolves out of thehydrogel over the encapsulation period, thus leaving pores of suitablesizes.

In some preferred embodiments, the pore size increasing agent ishydroxyethyl cellulose (HEC). In this embodiment, HEC may be used in thepreparation of the hydrogel; it is then completely, substantiallycompletely or partially removed from the hydrogel prior to use.Preferred concentrations of HEC in the hydrogel (during preparation)include 0.5-3.0% HEC, more preferably 1.0-2.5%, and even more preferably1.2-2.4% HEC. In some preferred embodiments, the concentration of HEC inthe hydrogel (during preparation) is about 1.2% or about 2.4%.(Concentrations are given as weight %). The HEC may be suspended in thegels as micelles. Removal of the HEC may be attained by washing thehydrogel in a suitable aqueous solvent or buffer, e.g. tissue culturemedium.

A pore size increasing agent could be of low molecular weight or of apolymeric nature. An example of a low molecular weight compound could besucrose that can be incorporated into a hydrogel in the form ofmicrocrystals and will dissolve over the encapsulation period.Alternatively it could be any water-soluble polymer. The advantage ofusing water-soluble polymers compared to small molecular weightcompounds is their slower dissolution profile allowing better controlover the pore size.

In other embodiments of the invention, the pore size increasing agentmay be a water-soluble polymer. Examples of suitable polymers includepoly(vinylpyrrolidone,), polyethyleneglycol, a high molecular weightglucose-based polymer (e.g. dextran, starch, pullulan), and acelluosecellulose-based polymer (e.g. hydroxypropylmethylcellulose,methylcelluose), methylcellulose, hydroxypropylcellulose,carboxymethylcellulose), poly(vinyl alcohol), polyacrylamide,poly(methyl vinyl ether), and block copolymers of polyethylene glycoland polypropylene glycol (e.g. Pluronics).

In some embodiments of the invention, the pore-size increasing agent isgelatin beads.

In some embodiments of the invention, the hydrogel still comprisesdetectable levels of the pore-size increasing agent, e.g. a watersoluble polymer.

In some embodiments of the invention, the gelling of the hydrogel isfacilitated using a compound comprising a multivalent metal cation, e.g.using calcium chloride. In particular, calcium chloride (e.g. 50-200 mMcalcium chloride, preferably 75-120 mM calcium chloride) may be used togel alignate hydrogels.

In other embodiments, of the invention, an alternative metal chloride isused, e.g. magnesium or barium or strontium chloride. Alternatively,other multivalent cations may be used, e.g. La³⁺ or Fe³⁺.

In some embodiments of the invention, the gels (preferably alginategels) additionally comprises CO₂. This may aid cell viability after cellstorage, particularly after storage under chilled conditions.

The invention further provides a process for preparing a hydrogel,comprising the step of gelling the hydrogel-forming polymer in thepresence of a Group 2 metal salt selected from the group consisting ofmagnesium and strontium salts.

The interstitial liquid may be any liquid in which polymer may bedissolved and in which the polymer may gel. Generally, it will be anaqueous liquid, for example an aqueous buffer or cell culture medium.The liquid may contain an antibiotic. Preferably, the hydrogel issterile, i.e. aseptic. Preferably, the liquid does not containanimal-derived products, e.g. foetal calf serum or bovine serum albumin.

The hydrogel comprises a plurality of individual cells retained therein.These cells are in general separated or dispersed within the hydrogel,i.e. the cells are not connected in the form of a tissue or organ.Preferably, the cells are primary cells. The cells are live or viablecells or substantially all of the cells are live or viable. In someembodiments of the invention, the cells are all of the same type. Forexample, they are all brain cells, muscle cells or heart cells. In otherembodiments, the cells are all from the same lineage, e.g. allhaematopoietic precursor cells. In some embodiments, the cells are stemcells, for example, neural stem cells or embryonic stem cells.Preferably the cells are mammalian cells.

In some preferred embodiments, the cells are adipocytes, astrocytes,blood cells, blood-derived cells, bone marrow cells, bone osteosarcomacells, brain astrocytoma cells, breast cancer cells, cardiac myocytes,cerebellar granule cells, chondrocytes, corneal cells, dermal papillacells, embryonal carcinoma cells, embryonic stem cells, embryo kidneycells, endothelial cells, epithelial cells, erythroleukaemiclymphoblasts, fibroblasts, foetal cells, germinal matrix cells,hepatocytes, intestinal cells, keratinocytes, keratocytes, kidney cells,liver cells, lung cells, lymphoblasts, melanocytes, mesangial cells,meningeal cells, mesenchymal stem cells, microglial cells, neural cells,neural stem cells, neuroblastoma cells, oligodendrocytes,oligodendroglioma cells, oral keratinocytes, organ culture cells,osteoblasts, ovarian tumour cells, pancreatic beta cells, pericytes,perineurial cells, root sheath cells, schwann cells, skeletal musclecells, smooth muscle cells, stellate cells, synoviocytes, thyroidcarcinoma cells, villous trophoblast cells, yolk sac carcinoma cells,oocytes, sperm and embryoid bodies. In some embodiments of theinvention, the cells are corneal cells.

In other preferred embodiments of the invention, the cells are cornealstem cells preferably comprising limbal epithelial cells, i.e. aheterogeneous mixture of stem cells and differentiated cells which isobtainable from the limbus at the edge of the cornea. In other words,the composition comprising corneal stem cells may comprise a mixture ofcorneal stem cells and cells that have not yet fully committed to acorneal epithelial phenotype. In other embodiments, the cells includestromal progenitor cells such as corneal fibroblasts (keratocytes) in andifferentiated or undifferentiated form. Preferably, these cornealfibroblasts are obtained from the peripheral limbus or from limbal ringswhich are incubated overnight with about 0.02% collagenase at about 37°C. In another preferred embodiment, the cells are bone marrow cells. Inother embodiments, the cells are chondrocytes. In yet other embodiments,the cells are epithelial cells.

As used herein, the term “suppressing or preventing cell division” meansthat the rate of cell division within all or a substantial proportion ofthe cells contained within the hydrogel (for a given temperature) is ata lower level than that of control cells which are maintained underappropriate tissue culture conditions at the same given temperature andwhich are not entrapped or encapsulated in a hydrogel. A substantialproportion may be at least 50%, 60%, 70%, 80%, 90% or 95%.

As used herein, the term “suppressing or preventing celldifferentiation” means that the rate of cell differentiation within allor a substantial proportion of the cells contained within the hydrogel(for a given temperature) is at a lower level than that of control cellswhich are maintained under appropriate tissue culture conditions at thesame given temperature and which are not entrapped or encapsulated in ahydrogel. A substantial proportion may be at least 50%, 60%, 70%, 80%,90% or 95%.

The cells are generally seeded into the hydrogel during the formation ofthe hydrogel from its constituent polymers, for example, by mixing thecells with a solution of the monomer prior to polymerization/aggregationor prior to cross-linking of a hydrogel-forming polymer.

For this reason, the hydrogel is gelled under appropriatecell-compatible conditions, i.e. conditions which are not detrimental ornot significantly detrimental to the viability of the cells.

In some embodiments of the invention, the concentration of cells whichare present in the hydrogel is 1×10³-1×10⁶ cells/ml hydrogel solution.Generally the concentration of cells is less than 5×10⁵, preferably0.1×10⁵-5×10⁵ cells/ml hydrogel, more preferably 0.5×10⁵-2.3×10⁵cells/ml hydrogel, and most preferably 1.0×10⁵-2.0×10⁵ cells/mlhydrogel. Particularly preferred cell concentrations include:

-   -   up to 2.5×10⁵ cells/ml for alginate gels maintained under cell        culture conditions;    -   up to 1.5×10⁵ cells/ml for alginate gels maintained under        ambient conditions;    -   up to 1.5×10⁵ cells/ml for an alginate gel disc maintained under        cell culture, chilled or ambient conditions.

In the invention, the cells are embedded in the hydrogel, i.e. the cellsare generally entrapped or encapsulated within the hydrogel and notmerely placed on a surface of a hydrogel.

The hydrogels may be produced in any suitable size. For ease oftransportation, however, the hydrogels are preferably less than 100 mmin length, preferably less than 50 mm in length. The thickness of thehydrogel is generally 0.1-5mm, preferably 1.0-2.0 mm, more preferablyabout 1.5 mm.

The volume of the hydrogels of the invention is preferably 0.2-100 ml,more preferably 0.2-50 ml, 0.2-25 ml or 0.2-10 ml. In some preferredembodiments, the volume of the hydrogel of the invention is 0.4-5 ml,preferably 0.4-4 ml, and more preferably 0.4-3 ml. In some embodimentsof the invention, the volume may be about 420 μl or about 2 ml.

In some embodiments of the invention, the hydrogel is in the form of athin layer or disc. The disc may for example, have a diameter of 5-50mm, preferably 10-30 mm, more preferably 15-25 mm, and most preferablyabout 19 mm. The thickness of the disc is generally 0.1-5mm, preferably0.5-2.0 mm, more preferably about 1.0 or 1.5 mm. In some embodiments,the volume of hydrogel in the disc is preferably 200-600 μl, preferably300-500 μl and more preferably 400-450 μl.

With regard to the discs of the invention, the preferred hydrogelpolymer concentration is about 1.2% due to the increased structuralstability provided by this concentration. Preferably, the hydrogel (e.g.a disc) is an uncompressed hydrogel, i.e. it has not been subjected toan axial compressing force.

In some embodiments, the hydrogels are prepared under GMP (GoodManufacturing Practice) conditions.

For transportation or delivery of the cells in the hydrogel, thehydrogel may be appropriately packaged. For example, the hydrogel may bephysically protected in order to prevent mechanical damage to thehydrogel. It may also be wrapped, treated or encased in order to preventwater loss.

During transportation and/or storage, the hydrogel comprising cells maybe maintained in contact with (e.g. fully or partially immersed in) anappropriate media. Suitable media include cell or tissue culture media,e.g. supplemented DMEM media.

For example, the hydrogel may be enclosed within a water-tight orair-tight material or container, e.g. a plastic container.Alternatively, the hydrogel may be contained within a vial or cryovialor tissue culture flask, optionally together with appropriate media(e.g. cell culture media). In other embodiments, the hydrogel may becontained within a sealed bag, with a controlled CO₂ level.

The cells may be transported by any suitable means, e.g. by post orcourier, which might include transportation by automotive means, e.g. bycar, van, lorry, motorcycle, aeroplane, etc. Preferably, thetransportation is by post or courier.

The second location is preferably a location which is remote from thefirst location, e.g. at least 1 mile, preferably more than 5 miles, fromthe first location.

In yet a further aspect, the invention provides a method for fulfillingan order or request for cells, the method comprising the steps: (i)receiving an order or request for cells; (ii) encapsulating orentrapping the desired cells in a hydrogel; (iii) dispatching thecell-containing hydrogel for transportation to the location specified inthe order or request; and optionally, (iv) transporting thecell-containing hydrogel to the location specified in the order orrequest.

The order or request may be received by any suitable means, e.g. via theinternet, email, text-message, telephone or post.

A particularly preferred embodiment of the invention relates to a 0.6%calcium alginate hydrogel comprising living cells.

A further particularly preferred embodiment of the invention relates toa 1.2% calcium alginate hydrogel comprising living cells, wherein thehydrogel is in the form of a thin layer or thin disc. Such a hydrogel isparticularly suitable for maintaining the viability of the cellsentrapped therein under ambient storage conditions, preferablyepithelial cells.

The invention further provides a process for the preparation of ahydrogel comprising living cells, the process comprising the steps: (i)gelling a hydrogel-forming polymer in the presence of living cells and awater-soluble pore size increasing agent; and (ii) dissolving all or asubstantial proportion of the pore size increasing agent out of thehydrogel.

The invention further provides the use a pore size increasing agent inthe preparation of a hydrogel. Preferably, the pore size increasingagent is HEC.

Additionally, the invention provides a process for the preparation of ahydrogel comprising living cells, the process comprising the step: (i)gelling a hydrogel-forming polymer in the presence of living cells andof a metal salt selected from the group consisting of magnesium andstrontium.

In other embodiments, the invention provides a process for thepreparation of a hydrogel comprising living cells, the processcomprising the step: (i) gelling a hydrogel-forming polymer in thepresence of living cells, wherein the hydrogel is gelled in the form ofa thin layer or disc.

The hydrogels may be stored during transportation or otherwise. Thehydrogels comprising living cells may be stored at −80° C. to 45° C.,preferably at 4 to 45° C. In some embodiments, the hydrogels are storedunder cell culture conditions (e.g. about 37° C., about 5% CO₂ and about95% humidity). In some embodiments, the hydrogels of the invention arestored under chilled conditions, e.g. 4-6° C., preferably about 4° C. Inother embodiments, the hydrogels of the invention are stored underambient conditions, e.g. 10-25° C., preferably 18-22° C. In someembodiments, the ambient temperature may be up to 30° C., or even up to40° C. In yet other embodiments, the hydrogels of the invention arestored at about 37° C.

In some embodiments of the invention, the hydrogel comprising cells isfrozen prior to storage and/or transportation. This may extend the timeduring which the cells are viable post-thawing and/or increase theusable transit-time. Hence the hydrogel may be used in this way as apost-cryoprotectant. For example, the temperature of the hydrogelcomprising cells may be reduced to below 0° C., below −15° C. or below−80° C.

The hydrogel comprising cells may or may not be allowed to defrost orthaw, i.e. to increase its temperature to above 0° C. during storageand/or transportation, preferably at a slow, controlled or uncontrolledrate of temperature increase. In other embodiments the hydrogels of theinvention are not chilled or frozen.

The hydrogel with living cells retained therein may be stored (e.g.during transportation) for up to 10 or 20 weeks. Preferably, the cellsare stored in the hydrogel for up to 1, 2, 3, 4, 5, 6, 7, 8, 9 or 10weeks before being released from the hydrogels.

More preferably, the cells are stored in the hydrogel for up to 1, 2, 3,4, 5, 6, 7, 8, 9 or 10 days before being released from the hydrogels.

The hydrogel referred to herein is one from which living cells can bereleased. In other words, after the preservation or storage or transportof the cells contained therein, the hydrogel is capable of beingdissociated thus allowing the release or removal of all or substantiallyall of the cells which were previously retained therein.

The hydrogel is dissociated under appropriate cell-compatibleconditions, i.e. conditions which are not detrimental or notsignificantly detrimental to the cells. Preferably, the hydrogel isdissociated by being chemically disintegrated or dissolved.

For example, alginate gels may be disintegrated in an appropriatealginate dissolving buffer (e.g. 0.055 M sodium citrate, 0.15 M NaCl, pH6.8).

Preferably, at least 50%, 60% or 70% of the cells remain viable afterstorage, more preferably at least 80%, 85%, 90% or 95% of the cellsremain viable after storage. Viability may be assessed by Trypan blueexclusion assay or other similar means. Other similar means include theMTT (3-(4,5-dimethylthiazol-2-yl)-2,5-diphenyltetrazolium bromide) assayand examination of cell colony formation post-extraction.

In other embodiments, the invention provides the use of a hydrogel asdescribed herein as a wound dressing. Thus in a further embodiment ofthe invention, there is provided a method of treating a wound or anillness caused by a wound in a subject, the method comprising contactingthe wound with a hydrogel of the invention. The invention furtherprovides a hydrogel of the invention for use as a wound dressing.

Also provided is the use of a hydrogel of the invention in themanufacture of a medicament for the treatment of wounds or an illnesscaused by a wound. In some embodiments, the wound may be due to injury(e.g. a burn, abrasion, laceration, or more traumatic injury such as abattlefield injury) or surgery or any other causes.

In a further embodiment, there is provided a method of aiding bloodclotting in a subject which is bleeding, the method comprisingcontacting the site of bleeding with a hydrogel of the invention. Theinvention further provides a hydrogel of the invention for use as ablood clotting agent.

Also provided is the use of a hydrogel of the invention in themanufacture of a medicament for the treatment of bleeding. The bleedingmay be from an external or internal surface or tissue.

In a further embodiment, the invention provides a method of treating anocular injury in a subject, the method comprising the steps: (a)providing a hydrogel comprising corneal stem cells; (b) contacting theocular injury with said hydrogel; and optionally (c) securing the saidhydrogel at the site of the ocular injury.

Ocular injuries that might be treated include those related to aninsufficient stromal micro-environment to support stem cell function,such as aniridia, keratitis, neurotrophic keratopathy and chroniclimbitis; or related to external factors that destroy limbal stem cellssuch as chemical or thermal injuries, Stevens-Johnson syndrome, ocularcicatricial pemphigoid, contact lens wear, or extensive microbialinfection.

Preferably, the subject is a mammal, most preferably a human. Suitablehydrogels have been described herein.

The hydrogel comprising corneal stem cells preferably comprises limbalepithelial cells, i.e. a heterogeneous mixture of stem cells anddifferentiated cells which is obtainable from the limbus at the edge ofthe cornea. In other words, the hydrogel comprising corneal stem cellsmay comprise a mixture of corneal stem cells and cells that have not yetfully committed to a corneal epithelial phenotype.

As used herein, the term “corneal” cells refers to cells which have beenobtained from an animal (preferably mammalian) cornea. Preferably, thecells are obtained from the limbal ring of the cornea, i.e. the outeredge of the cornea excluding the conjunctiva, iris and central cornea.The cells may comprise or consist of epithelial cells. The cells maycomprise or consist of corneal stem cells, preferably limbal cornealepithelial stem cells. Preferably, the corneal stem cells are humancorneal stem cells.

The cells are preferably isolated within a GMP facility or surgicaltheatre. The cells may be obtained from the subject to be treated, froma relative of the subject to be treated or from non-related donor. Insome embodiments, the cells may be derived from a non-damaged eye fromthe subject to be treated.

Preferably, the cells are obtained from the same species as the subject.

The damaged ocular surface may be prepared by removing diseased cellsand/or tissue. This may be done using standard surgical procedures, inorder to expose the underlying corneal stroma. The hydrogel comprisingcorneal stem cells may then be placed onto or over the damaged ocularsurface, e.g. onto or over the corneal stroma. The hydrogel may besecured in place by appropriate means, e.g. using a therapeutic contactlens or inserting the hydrogel under the conjunctiva (the membranesurrounding the cornea), e.g. by first separating the conjunctiva fromthe sclera, then pulling the conjunctiva across the cornea and hydrogelgel. An appropriate suture, e.g. a purse string suture, may be used. Theconjunctiva is now covering both the hydrogel and the cornea. Atherapeutic contact lens might also be used to cover the conjunctiva.Optionally, the eyelid may be sutured closed to prevent infection and/orto maintain the position of the hydrogel, e.g. for 1 to 14 days.

In yet a further embodiment, the invention provides a method of treatinga subject having a damaged ocular surface, the method comprising thesteps: (a) providing a hydrogel comprising corneal stem cells and/orgrowth factors secreted or secretable by corneal stem cells; (b)optionally removing diseased cells and/or tissue from the damaged ocularsurface of the subject; (c) contacting the damaged ocular surface withsaid hydrogel; and (d) optionally securing the said hydrogel at the siteof the damaged ocular surface.

The invention further provides a method of treating a damaged ocularsurface in a subject, the method comprising the steps: (a) providing ahydrogel comprising corneal stem cells and/or growth factors secreted orsecretable by corneal stem cells; (b) optionally removing diseased cellsand/or tissue from the damaged ocular surface of the subject; (c)contacting the damaged ocular surface with said hydrogel; and (d)optionally securing the said hydrogel at the site of the damaged ocularsurface.

As the hydrogel dissolves and/or disaggregates, it will release limbalcell derived growth factors and/or the limbal cells to the damagedocular surface. Transplanted cells may either directly repopulate .thedamaged ocular surface or facilitate the recruitment oftherapeutically-advantageous host cells to the wound site, therebyregenerating the damaged ocular surface. The hydrogel will be washedaway gradually via the tear duct and then excreted via the kidneys, orwashed directly away from the surface of the eye by a clinician. Excesstransplanted cells may also be removed by similar means after a periodof weeks, e.g. 1-4 weeks.

Any of the method of treating steps may be combined with any of themethods of transporting cells, methods of preparing cells, methods offulfilling an order, methods of suppressing or preventing cell divisionsteps described herein.

For example, the invention provides a method of treating an ocularinjury in a subject, the method comprising the steps: (a) encapsulatingor entrapping corneal stem cells in a hydrogel; (b) transporting thecell-containing hydrogel from a first location to second location; (c)contacting the ocular injury with said hydrogel; and optionally (d)securing the said hydrogel at the site of the ocular injury.

In addition to the hydrogel, one or more other agents may be applied tothe eye, e.g. an antibiotic, an anti-inflammatory agent, etc.

The invention further provides a hydrogel comprising corneal stem cellsand/or growth factors secreted or secretable by corneal stem cells foruse in therapy or for use as a medicament.

The invention further provides a hydrogel comprising corneal stem cellsand/or growth factors secreted or secretable by corneal stem cells foruse in treatment of an ocular injury or in treatment of a damaged ocularsurface.

The invention further provides the use of a hydrogel comprising cornealstem cells and/or growth factors secreted or secretable by corneal stemcells in the manufacture of a composition or medicament for treatment ofan ocular injury or in treatment of a damaged ocular surface.

It will be appreciated that the disclosures herein relating to hydrogelsapply, mutatis mutandis, to the methods of treating aspects of thisinvention. In this context, the hydrogel is preferably a 0.6-2.4%alginate gel, e.g. sodium or calcium or strontium alginate gel,preferably strontium alginate gel, optionally produced using a poreincreasing agent (e.g. HEC) as described herein.

Particularly advantageous results have been obtained by using hydrogelsin the form of a thin layer or disc or sheet. Hydrogels in such formsare shown herein to enhance the viability of cells. The thin layer ordisc or sheet is preferably isolated.

Preferably, the gel is in the form of a disc or thin layer. The diameterof the disc is preferably 10-50 mm. The final volume of the gel ispreferably 1-5 ml. The thickness of the thin layer or disc or sheet ispreferably 0.1-5 mm, e.g. about 1, 2, 3, 4 or 5 mm.

In yet a further embodiment, the invention provides a kit for producinga hydrogel comprising living cells, the kit comprising: (a) ahydrogel-forming polymer; and (b) a population of living cells.Additionally, the kit may comprise one or more of the following: (c) aninterstitial liquid; (d) a pore-size increasing agent, preferably awater-soluble pore-size increasing agent; (e) a mould for forming a gel;(f) instructions for the preparation of a hydrogel comprising livingcells; (g) packaging to prevent mechanical damage to the hydrogel; (h)an address label.

In some particularly preferred embodiments of the invention, thehydrogel comprises 1.2% alginate and the pore size increasing agent is1.2% HEC; and such gels are stored at ambient temperature.

It has been found that the mechanical strength of the hydrogel may beenhanced by the encapsulation of a reinforcing structure, scaffold ormesh within the gel. It may be synthetic or natural polymer. Preferably,the reinforcing structure, scaffold or mesh is biodegradable. Thereinforcing structure, scaffold or mesh may, for example be a polymercomprising polylactic acid (e.g. poly(lactic acid-co-caprolactone)(PLACL)), collagen or nylon.

In yet other embodiments of the invention, the hydrogel comprises anylon mesh. Such a composite material has the advantage of being morerobust than an alginate gel and less likely to break up during storageor transit of the gel. A further benefit is that the nylon mesh may besutured, thereby allowing the gel to be held by stitches. The nylon meshmay be within the gel, partially within and partially outside the gel oroutside (i.e. on a surface of) the gel. The nylon mesh preferably has amesh size of 0.01-100 μm. Preferably, it is made of a suitable non-toxicmaterial, which may be soluble or insoluble.

In a preferred embodiment, the hydrogel is in the form of a disccomprising a nylon mesh. Preferably, the nylon mesh is embedded withinthe disc.

BRIEF DESCRIPTION OF THE FIGURES

FIG. 1. The viability of a corneal epithelial cell-line in calciumalginate gel masses is dependent on polymer concentration, period ofencapsulation and storage condition. HCE cells extracted from 0.3%, 0.6%and 1.2% calcium alginate gel masses maintained for 1, 3, 5, 7 and/or 12days under cell culture (A, D), ambient (B, E) and chilled (C, F)conditions were washed and suspended in medium. Numbers of live and deadcells were assessed by Trypan blue exclusion. Proportions of live cellswere expressed as a percentage of total cells (100%) extracted fromgels. Data points represent the mean (n=3) percentage live cellsextracted. * P≦0.05 indicate differences between alginateconcentrations.

FIG. 2. Corneal epithelial cells extracted from calcium alginate gelmasses are able to adhere and assemble into colonies. HCE cellsextracted from calcium alginate gel masses maintained for 7 days undercell culture (alginate concentrations—0.3%: A, 0.6%: B, 1.2%: C) and 5days under ambient (alginate concentrations—0.3%: D, 0.6%: E, 1.2%: F)and chilled (alginate concentrations—0.3%: G, 0.6%: H, 1.2%: I)conditions were washed and suspended in medium. Cells were cultured at37° C. under 5% CO₂ and 95% humidity. Images of cell colonies (100×magnification) represent 3 individual experiments.

FIG. 3. SEM microphotographs of calcium alginate gels. Calcium alginategel masses (0.3%: A, 0.6%: B and 1.2%: C) were dehydrated and internalsurfaces were examined using SEM. Electron micrographs (19000×magnification) represent 3 individual experiments.

FIG. 4. The viability of limbal epithelial cells within calcium alginategel masses is influenced by storage conditions. Limbal epithelial cellsextracted from 0.6% calcium alginate gel masses maintained for 1, 3, 5and 7 days under cell culture, ambient or chilled conditions were washedand resuspended in medium. Numbers of live and dead cells were assessedby Trypan blue exclusion. Proportions of live cells were expressed as apercentage of total cells (100%) extracted from gels. Data pointsrepresent the mean (n=3) percentage live cells extracted. * P≦0.05indicate differences between storage conditions.

FIG. 5. Limbal corneal epithelial cells extracted from calcium alginategel masses are able to adhere and assemble into colonies. Limbalepithelial cells extracted from 0.6% calcium alginate gel massesmaintained for 5 days under cell culture (A) and chilled (B) conditions,were washed and resuspended in medium. Cells from individual conditionswere cultured in supplemented medium 37° C. under 5% CO₂ and 95%humidity. Images of cell colonies (100× magnification) represent 3individual experiments.

FIG. 6. Calcium alginate gel masses and discs. Calcium alginate wasprepared into 0.6% gel masses (A, C) and 1.2% gel discs (B, C). Gelmasses were approximately 12.5 mm in length (A) and 6 mm in depth(C),whereas gel discs were approximately 19 mm in length (B) and 1.5 mmin depth (C). Images (100× magnification) represent 3 individualexperiments.

FIG. 7. Limbal epithelial cell viability is enhanced within a thin discof calcium alginate gel. Limbal epithelial cells extracted from 1.2%calcium alginate gel discs maintained for 1, 3, 5 and 7 days under cellculture, ambient or chilled conditions, were washed and resuspended inmedium. Levels of viable cells were measured using Trypan blue exclusionassay (A, B) and functional cells were assessed using the MTT assay (C).Proportions of live cells were expressed as a percentage of total cells(100%) extracted from gels (A). Data points represent the mean (n=3)percentage live cells extracted. * P≦0.05 indicate differences betweenstorage conditions.

FIG. 8. Limbal epithelial cells extracted from calcium alginate geldiscs are able to adhere and assemble into colonies. Limbal epithelialcells extracted from 1.2% calcium alginate gel discs maintained for 7days under cell culture (A), ambient (B) and chilled (C) conditions,were washed and resuspended in medium. Cells were added to supplementedmedium and cultured at 37° C. under 5% CO₂ and 95% humidity. Images ofcell colonies (100× magnification) represent 3 individual experiments.

FIG. 9A-B. Corneal epithelial cell viability is enhanced within calciumalginate gels modified with HEC. A: Corneal epithelial cells extractedfrom 2.4% calcium alginate discs, 1.2% alginate:1.2% HEC discs and 2.4%alginate:2.4% HEC discs maintained for 3 days under cell cultureconditions, were washed and resuspended in medium. Levels of viablecells were measured using Trypan blue exclusion assay. Proportions oflive cells were expressed as a percentage of total cells (100%)extracted from gels. Data points represent the mean (n=2) percentagelive cells extracted. B: 1.2% alginate, 1.2% alginate:1.2% HEC and 1.2%alginate:2.4% HEC gels were similarly compared.

FIG. 10. SEM microphotographs of calcium alginate and calciumalginate/HEC gels. Calcium alginate gel discs were dehydrated andinternal surfaces were examined using SEM. Electron micrographs (19000×magnification) represent 3 individual experiments. The references inFIGS. 9A and 10 to “4-HEC” refer to HEC.

FIG. 11. Corneal epithelial cell viability in HEC-modified alginate geldiscs correlations with the mechanical properties of gels. The viabilityof HCE cells extracted from alginate or HEC-modified alginate gel discswas assessed by Trypan blue exclusion. Proportions of live cells wereexpressed as a percentage of total cells (100%) initially encapsulatedwithin gels (highlighted in black circles). The compressive moduli ofgels was obtained by measuring their yield point with a trigger force of0.0005 N. Data points for cell viability represent the mean (n=3)percentage live cells extracted and data points for compressive modulirepresent 10 individual measurements.

FIG. 12. Picture of calcium alginate gel disc (1.2%) with nylon meshinside. Alginate gel disc is approximately 20 mm in length (A), and isreadily transferred by forceps (B).

FIG. 13. hMSC and mESC were found to be evenly distributed within thestrontium alginate gel as shown by propidium iodide nuclear staining.

FIG. 14. The percentage of total cell survival following storage ineither alginate-nylon gel discs or cryopreservation. Error barsrepresents standard deviation.

FIG. 15. The percentage of relative cell survival following storage ineither alginate-nylon gel discs or cryopreservation. Error barsrepresents standard deviation.

FIG. 16. Comparison between mESC and hMSC prior to encapsulation andfollowing extraction from alginate gels after 5 days encapsulation. mESCcolonies were found under both conditions prior to encapsulation (A),and following alginate gel encapsulation (B). Spindle shaped hMSC alsoshowed no notable differences prior to (C) or following (D)encapsulation.

FIG. 17. Cell-doubling time (hours). No significant differences wereseen between either hMSC or mESC prior and following gel encapsulation.Unit of x-axis: hours.

FIG. 18. hMSC markers detection of hMSC in optimal culture condition,preserved in alginate gel condition and cryopreservation condition. Allthree of MSC markers showed increased mRNA level after alginate andcryopreservation storage.

FIG. 19. mESC markers detection of mESC in optimal culture condition,preserved in alginate gel condition and cryopreservation condition. mESCextracted from alginate gel showed relatively highest value of bothOct-3/4 and SSEA1 markers.

FIG. 20. Expression of mESC markers between mESC encapsulated withinalginate gel and cryopreserved in liquid nitrogen by flow cytometry.mESC's were studied immediately following release form a 5 day storage(alginate or cryopreservation). Cells were also studied following 10days in standard culture media post-storage. Cryopreservation resultedin a considerable, albeit temporary loss of OCT3/4 and SSEA4 expression.No difference was seen between alginate-encapsulated cells.

FIG. 21. Total cell viability (viable cells extracted/total numberencapsulated) following 5 days at ambient storage. Results show successacross a range of cell types including immortalised cell lines, primarycells and stem cells.

EXAMPLES

The present invention is further defined in the following Examples, inwhich parts and percentages are by weight and degrees are Celsius,unless otherwise stated. It should be understood that these Examples,while indicating preferred embodiments of the invention, are given byway of illustration only. From the above discussion and these Examples,one skilled in the art can ascertain the essential characteristics ofthis invention, and without departing from the spirit and scope thereof,can make various changes and modifications of the invention to adapt itto various usages and conditions. Thus, various modifications of theinvention in addition to those shown and described herein will beapparent to those skilled in the art from the foregoing description.Such modifications are also intended to fall within the scope of theappended claims.

The disclosure of each reference set forth herein is incorporated hereinby reference in its entirety.

Example 1 Materials and Methods Culture of a Human Corneal Epithelial(HCE) Cell-Line

A human corneal epithelial (HCE) cell-line was cultured in Dulbecco'sminimal essential medium (DMEM) and Ham's F12 medium (DMEM/F12,1:1),supplemented with 10% fetal bovine serum (FBS: Hyclone, UK), 0.5%dimethylsulphoxide (DMSO: Sigma-Aldrich, Poole, UK), 10 ng/ml humanepidermal growth factor (hEGF: Sigma-Aldrich, Poole, UK), 5 mg/nilinsulin (Sigma-Aldrich, Poole, UK), 100 IU/m1 penicillin and 100 mg/mlstreptomycin at 37° C. under 5% CO₂ and 95% humidity. Cells werereplenished with fresh medium every 3 days and grown to 70-80%confluency.

Isolation of Epithelial Cells from the Cornea

The established bovine cornea model (20-21) was used for the isolationof limbal epithelial cells. Normal bovine eyes were obtained from alocal abattoir (Chity whole sale abattoir, Guildford, UK) within 2 h ofdeath, transported to the laboratory at 4° C. and used immediately.Corneoscleral buttons were dissected using standard eye bank techniques,as previously described (22).

Encapsulation of Epithelial Cells in Calcium Alginate Gel Masses andDiscs

HCE and limbal epithelial cells were suspended in 0.3%, 0.6% and/or 1.2%(w/v) sodium alginate solutions before gelling into masses and discsusing 102 mM CaCl₂, as described previously (23). Gel masses and discswere formed by pipetting 2 mL sodium alginate/cell solutions into 102 mMCaCl₂ and using chromatography paper molds (Whatman) immersed in 102 mMCaCl₂ respectively.

Calcium alginate gel masses and discs were suspended in supplementedDMEM/F12 medium under cell culture (37° C., 5% CO₂, 95% humidity),ambient (18-22° C., atmospheric CO₂ and humidity levels) and chilled (4°C., atmospheric CO₂ and humidity levels) conditions, for 1, 3, 5, 7and/or 12 days. Under cell culture storage, gels were seeded with 5×10⁵cells/2 mL gel. Initial experiments performed under ambient and chilledconditions using gels seeded with 5×10⁵ cells/2 mL gel, demonstrated arapid decline in cell viability, that was prevented by reducing cellnumbers to 3×10⁵ cells/2 mL gel; periods of encapsulation wererestricted to 7 days as cells did not remain alive for longer periods oftime. Gel/cell matrices were replenished with fresh medium every 2 days.Loss of cells from calcium alginate gel masses due to the extractionprocess was minimal.

Cell Viability Analysis

Cells were extracted from calcium alginate gel masses and discs usingalginate dissolving buffer (0.15 M NaCl, 0.055 M sodium citrate). Cellsfrom individual conditions were cultured in supplemented DMEM/F12 forapproximately 3 days for HCE and 2 weeks for limbal epithelial cells tomonitor the ability of these cells to attach and form coloniespost-extraction. Images of cell colonies were obtained at 100×magnification. The Trypan blue exclusion assay was performed by mixing a10 μL cell suspension with 10 μL Trypan blue dye solution (v/v), beforecounting live (unstained) and dead (stained-blue) cells using ahaemocytometer. The MTT(3-(4,5-dimethylthiazol-2-yl)-2,5-diphenyltetrazolium bromide) assay wasperformed to assess cell metabolic activity, following themanufacturer's protocols. Briefly, 12 mM3-(4,5-dimethylthiazol-2-yl)-2,5-diphenyltetrazolium bromide was addedto a 100 μL suspension of cells and this was incubated for 2 h at 37° C.Cells were then lysed using dimethylsulphoxide (DMSO), incubated for afurther 10 min at 37° C., mixed and the absorbance of the reactionproduct (formazan) was measured at 540 nm.

Scanning electron microscopy (SEM) analysis of calcium alginatestructure

The internal surfaces of 0.3%, 0.6% and 1.2% calcium alginate gels wereexamined by SEM. Gels were fixed in 1.25% (v/v) glutaraldehyde andpost-fixed for 2 hours in 1% aqueous osmium tetroxide, washed indistilled water and passed through a graded ethanol series (50%, 70%,90% and 100%) before dehydration through critical point drying.Dehydrated gels were mounted on aluminium stubs and sputter coated withgold before examination using SEM (FEI Quanta FEG 600, UK).

Statistical Analysis

Unpaired Student's t-tests were performed using Microsoft Excel. Resultsare presented as the mean of 3 individual experiments with standarderror of mean and P-value 0.05 considered significant.

Results Calcium Alginate Supports Corneal Epithelial Cell Viability in aDifferential Manner Under Various Storage Conditions

The ability of a calcium alginate gel to support viable cornealepithelial cells was investigated to examine the suitability of this gelscaffold for the preservation of live cells intended for therapeuticpurposes. Immortalised human corneal epithelial (HCE) cells 5, 7 and/or12 days and stored under cell culture (37° C., 5% CO₂, 95% humidity),ambient (18-22° C., atmospheric CO₂ and humidity levels) and chilled (4°C., atmospheric CO₂ and humidity levels) conditions.

Cell viability was assessed by the Trypan blue exclusion assay and cellattachment and colony formation post-extraction. Proportions of live anddead cells measured using the Trypan blue exclusion assay were expressedas percentages of the total number of cells (100%) extracted from gels.

The viability of corneal epithelial cells within calcium alginate wasinfluenced by polymer concentration, period of encapsulation and storagecondition (FIG. 1). Cell viability decreased with increased periods ofencapsulation under all storage conditions investigated. Similarproportions of viable cells were recovered from calcium alginate gelsmaintained under cell culture (32-49%) and chilled (35-51%) conditionsover 7 and days respectively (compare FIG. 1A and 1C), but cells fromcell culture storage assembled into larger colonies (FIG. 2A-2C) thanthose from ambient (FIG. 2D-2F) or chilled (FIG. 2G-2I) storage.

Gels comprising 0.3% or 0.6% alginate supported greater levels of viablecells than 1.2% alginate gels under cell culture (FIG. 1A and 1D),ambient (FIG. 1B and 1E) and chilled (FIG. 1C and 1F) storage. Althoughlive cells extracted from both 0.3% and 0.6% alginate gels were able toadhere and assemble into colonies, cells recovered from 0.6% alginategels (FIG. 2B) formed larger colonies than those from 0.3% alginate gels(FIG. 2A). This pattern of growth was particularly apparent underambient (FIG. 2D-F) and chilled (FIG. 2G-I) conditions.

The numbers of cells recovered from 0.3% alginate gels were consistentlylower than those extracted from 0.6% alginate gels under cell culturestorage (FIG. 1D), possibly due to loss of cells from the loosestructure (data not shown) of 0.3% alginate gels. The reduction in cellviability in 1.2% alginate gels, however, may be due to detrimentaleffects of the increased alginate concentration within this gel matrix,as a 0.6% alginate gel retained a significantly greater (P≦0.05) numberof live cells than a 1.2% alginate gel (FIG. 1D). Dead or apoptoticcells may have contributed to the reduction in cell viability andrecovery, as the phagocytic cells necessary for their clearance (24-25)were not incorporated within gels.

Taken together, these data demonstrated that a 0.6% alginate gel masswas more suitable for maintaining viable epithelial cells than gelmasses containing 0.3% and 1.2% alginate, under cell culture, ambient orchilled storage conditions.

Example 2 The Structure of Calcium Alginate Gels may Influence theViability of Encapsulated Cells

As corneal epithelial cell viability varied within differentconcentrations of calcium alginate, potential links between thestructure of this gel and its ability to support viable cells wereinvestigated. Calcium alginate gel masses (0.3%, 0.6% and 1.2%) werechemically dehydrated and internal surfaces were exposed and coated withgold, before analysis of their morphology using scanning electronmicroscopy (SEM).

The internal structure of calcium alginate gel masses comprised ofirregular pore spaces with dimensions which increased with decreases inalginate concentration (FIG. 4). Pore diameters ranged from 0.2-3.0 μmwithin a 0.3% alginate gel (FIG. 4A), 0.1-1.0 μm within a 0.6% alginategel (FIG. 4B) and 0.1-0.4 μm within a 1.2% alginate gel (FIG. 4C).Previous reports showed that solutes migrated at a slower rate through a3% alginate gel with small pores than through a 1.5% alginate gel withrelatively larger pores (6). Therefore, the greater viability of cellsin 0.3% and 0.6% alginate gels than 1.2% gels may potentially be due totheir more ready access to medium nutrients moving more efficientlythrough pore spaces which are larger than those within 1.2% alginategels.

Example 3 Limbal Epithelial Cell Viability in Calcium Alginate GelMasses is Affected by Storage Conditions

To understand the extent of corneal epithelial cell viability withincalcium alginate gels in a potentially therapeutic context, epithelialcells isolated from the corneal limbus (bovine model) were encapsulatedwithin this gel. Cells were encapsulated in 0.6% calcium alginate, asthis concentration of the gel supported viability more robustly thangels containing 0.3% or 1.2% alginate (see FIGS. 1 and 2). Cellviability was examined over 1, 3, 5, and 7 days under cell culture,ambient and chilled storage conditions by the Trypan blue exclusionassay and cell colony/sheet formation post-extraction.

Limbal epithelial cell viability was supported most robustly underchilled and cell culture conditions in 0.6% alginate gel masses. After1, 3, 5 and 7 day encapsulation periods, 10%, 50%, 35% and 5% more livecells respectively were extracted from calcium alginate gels underchilled conditions than from those stored under cell culture conditions.Post-extraction, however, cells from cell culture storage formed largesheets whereas those from chilled storage only assembled into smallcolonies (FIG. 5), possibly indicating that live cells from chilledstorage were too damaged to adhere.

Under ambient storage, limbal epithelial cell viability was very poor;cells did not remain alive for longer than 3 days (FIG. 4).

Example 4 The Viability of Limbal Epithelial Cells is Enhanced Ii ThinDiscs of Calcium Alginate

The effect of gel shape (thickness) on recovery of live limbalepithelial cells was examined. The gel was modified from an amorphousmass (approximately 6 mm depth and 12.5 mm width) to a thin disc(approximately 1.5 mm depth and 19 mm width) that presented a shorterdistance (FIG. 6) for movement of medium nutrients to, and wasteproducts from encapsulated cells.

A 1.2% alginate gel that formed structurally more stable discs than 0.3%and 0.6% alginate gels was used, despite the lower levels of viabilityachieved using this concentration of the gel (see FIG. 1), as it washypothesised that the reduced depth of the gel would compensate for lowcell viability. Cell viability was assessed using the Trypan blueexclusion assay and by examining cell colony/sheet formationpost-extraction. To determine whether the difference in limbalepithelial cell attachment and colony formation between cell culture andchilled storage cells (see FIG. 5) was due to differences in levels ofactive live cells, the MTT assay was used to measure cell metabolicactivity.

Limbal epithelial cell viability was enhanced in calcium alginate geldiscs compared to calcium alginate gel masses, as ambient storage thatwas demonstrated previously as unable to support viable cells for longerthan 3 days in gel masses (see FIG. 4), supported greater levels ofviable cells in discs over 1-7 days than cell culture and chilledstorage (FIG. 7). Under ambient storage, approximately 65-80% ofextracted cells were alive during 1-7 days of encapsulation in alginategel discs, and at least 70±7% of the total number of encapsulated cells(3×10⁵) in these gels remained alive after 7 days (FIG. 7A). Proportionsand numbers of live cells extracted from gel discs maintained underambient storage over 1 and 7 days were significantly greater (P≦0.05)than those extracted from gel discs under chilled storage (FIG. 7A and7B).

As observed within alginate gel masses (see FIG. 4), the lowest levelsof viable cells were extracted from gels maintained under cell cultureconditions (FIG. 7A and 7B). Live cells extracted from cell culturestorage gel discs were, however, able to assemble into cell sheets (FIG.8A) similar to live cells extracted from gel discs maintained underambient storage (FIG. 8B). Only single cells from chilled storage geldiscs adhered (FIG. 8C), and the numbers of live metabolically active(FIG. 7C) and total live (FIG. 7B) cells from chilled storage weresimilar. Therefore, the inability of chilled storage live cells toassemble into colonies or sheets was not due to reduced levels ofmetabolically active cells.

Collectively, these data demonstrated that modification of themacro-structure of a calcium alginate gel from an amorphous mass to athin disc enhanced limbal epithelial cell viability, and overcame thereduction in cell viability observed with increases in alginateconcentration.

Example 5 Gels Modified Using HEC

To improve the ability of a Ca²⁺ alginate hydrogel to support viableencapsulated cells, a gel was made as described above but modifiedthrough the addition of hydroxyethyl cellulose (HEC).

A 2.4% alginate gel containing 2.4% HEC supported 50% greater levels oflive cells than a gel containing 2.4% alginate alone (FIG. 9A). Cellviability was enhanced in a 1.2% alginate:1.2% HEC gel compared to a2.4% alginate:2.4% HEC gel (FIG. 9). A 1.2% gel supported lowerproportions of viable cells compared to a 1.2% alginate:1.2% HEC gel(FIG. 9B).

The sizes of pore spaces correlated with cell viability (FIG. 10).Greater levels of viable cells were retrieved from gels with largeinternal pores than from those with relatively smaller internal pores(compare 2.4% alginate with 2.4% alginate:2.4% HEC and compare 2.4%alginate:2.4% HEC with 1.2% alginate:1.2% HEC).

Example 6 Use of Hydrogels as Carriers for Cell TransplantationIsolation of Limbal Stem Cells

Isolation occurs within a GMP facility or surgical theatre. Tissuepieces approximately 10 mm×5 mm×1 mm in size containing epithelial cells(a proportion of which will be adult stem cells) and underlying stromafrom the limbus (the anatomical region of the eye between the whitesclera and transparent cornea) is surgically removed by scissors orblade from either donor or contralateral eye. The epithelial cells aredissociated from the tissue using a combination of agitation and enzymedigestion (enzymes include collagenase, dispase, trypsin/EDTA, liberase)for a period between 10 mins and 2 hours at 37° C. in basal culturemedium. After this time, the epithelial cells are separated from therest of the tissue, thereby creating a suspension of limbal epithelialcells containing stem cells.

Encapsulation of Isolated Cells

The number of isolated viable cells is quantified using an automatedcell counter. A known number of limbal cells (1×10³ to 1×10⁶ cells/1 mLof sodium alginate solution) is encapsulated in calcium alginate gels.Gels are formed in discs by the addition of calcium chloride to 0.6-2.4%sodium alginate containing or not containing HEC using circular mouldswith a diameter of 1-5 cm. The final volume of the gel is 1-5 ml with athickness of 0.1-5 mm.

Transplantation of Encapsulated Limbal Epithelial Cells

The damaged ocular surface is first prepared by removing diseased cellsand tissue using standard surgical procedures to expose the underlyingcorneal stroma. A disc of calcium alginate gel containing limbalepithelial cells is placed on to the corneal stroma and held in place byeither a therapeutic contact lens or inserting under the conjunctiva(membrane surrounding the cornea) by first separating the conjunctivafrom the sclera, then the conjunctiva is pulled across the cornea andalginate gel using a purse string suture. The conjunctiva is nowcovering both the alginate gel and the cornea. A therapeutic contactlens might also cover the conjunctiva. Finally the eyelid may be suturedclosed to prevent infection and to maintain the position of the alginategel.

Therapeutic Effect

As the alginate gel dissolves/disaggregates it will release limbal cellderived growth factors and/or the limbal cells to the damaged ocularsurface. Transplanted cells will either directly repopulate the damagedocular surface or facilitate the recruitment oftherapeutically-advantageous host cells to the wound site, therebyregenerating the damaged ocular surface.

The alginate gel will be washed away gradually via the tear duct andthen excreted via the kidneys, or washed directly away from the surfaceof the eye by a clinician. Excess transplanted cells will also beremoved by similar means after a period of 1-4 weeks.

Example 7 Determination of M/G Ratios of Alginate Gels

Alginate solution was prepared in deionised water at a concentration of2.5% (w/v). Alginate solutions (5 cm³ aliquots) were placed in 10 cm³glass microwave tubes (CEM) and subjected to microwave irradiation usinga power input of 200 W, a nominal temperature of 120° C. and a hold timeof 5 minutes. This method was adapted from the microwave-assisted rapidhydrolysis method of Chhatbar et al. (Chhatbar M., et al. “Microwaveassisted rapid method for hydrolysis of sodium alginate for M/G ratiodetermination”. Carbohydr. Polym. 2009; 76: 650-656), by using aresearch microwave reactor (CEM Discover LabMate) instead of a domesticmicrowave oven. The safety cut-off pressure of 200 psi was neverreached. Following hydrolysis, the M/G ratio was determined withreference to the method of Chandia et al. (Chandia NP, et al. “Alginicacids in Lessonia trabeculata: characterization by formic acidhydrolysis and FT-IR spectroscopy”. Carbohydr. Polym. 2001; 46: 81-87).Briefly, the hydrolysed solution was adjusted to pH 2.85 (monitored witha Mettler Toledo SevenEasy pH meter S20) using 0.1 M HCl (Fisher)solution and the resulting precipitate, poly(guluronic acid) wascollected by centrifugation (Denley BS400) and weighed. The supernatantwas adjusted to pH 1.0 using 0.1 M HCl solution and the secondprecipitate, poly(mannuronic acid) was collected by centrifugation andweighed.

The value obtained for the M/G ratio was 3.3±0.3 (77% M/23% G),consistent with the manufacturer's assertion that this alginate has ahigh M content.

Example 8 Analysis of the Compressive Mechanical Moduli of CalciumAlginate/HEC Hydrogels

Gel spheres were formed by dispensing 2 mL alginate or alginate/HECsolutions dropwise into 30 mL CaCl₂ (100 mM). Gelled spheres weremechanically tested at 1, 5, 10, 15, 20, 25, 30, 45 and 60 min todetermine the time periods needed for complete gelation. Alginate andalginate/HEC solutions gelled into stable gels after 10-20 min exposureto 102 mM CaCl₂. Mechanical testing of gels was achieved by compressingthese structures using a TA.XT.plus Texture Analyser (Stable MicroSystems, Surrey, UK) with a 5 kg load cell and a P/1 KS flat endedstainless steel probe (Stable Micro Systems, Surrey, UK) with a 1 cm²surface area. Measurement of the force was taken, with a trigger forceof 0.0005 N, and the yield point of gel spheres (point at which the gelssplit) was recorded. Force was recorded as the mechanical limit of thegels, described as comparative yield force and 10 measurements of eachgel sample were performed. The results are shown in FIG. 11.

Example 9 Use of Alginate Hydrogel as a Stem Cell Transportation DeviceMaterials and Methods Culture of Mouse Embryonic Stem Cells

Mouse embryonic stem cells (mESC) were cultured in Dulbecco's modifiedeagle's medium (DMEM) (Stemcell technologies, U.K.), supplemented with10% fetal bovine serum (FBS) (Stemcell technologies, U.K.), 0.2%2-mercaptoethanol (Life technologies, U.K.), 1% nonessential amino acid(Stemcell technologies, U.K.), 10 μg/ml leukemia inhibitor factor (LIF)(Stemcell technologies), 100 IU/ml penicillin and 100 mg/ml streptomycin(Invitrogen), in 0.1% gelatin (Life technologies, U.K.) coated T75flasks (Greiner CellStar®, U.K.) at 37° C. under 5% CO₂ and 95%humidity. Cells were replenished with fresh medium every 3 days andgrown to 70-80% confluence.

Culture of Human Mesenchymal Stem Cells

Human mesenchymal stem cells (hMSC) were cultured in low glucose DMEM(Life technologies, U.K.), supplemented with 10% FBS (Life technologies,U.K.), 100 IU/ml penicillin and 100 mg/ml streptomycin (Lifetechnologies, U.K.), at 37° C. under 5% CO₂ and 95% humidity. Cells werereplenished with fresh medium every 3 days and grown to 70-80%confluence.

Encapsulation of Mesenchymal and Embryonic Cells in Strontium AlginateGel Discs

3×10⁵ (viable cells) of hMSC were suspended in 1.2% (w/v) sodiumalginate solution with 1.2% (w/v) HEC, or 3×10⁵ (viable cells) of mESCwere suspended in 1.2% (w/v) sodium alginate solution, before gellinginto discs using 102 mM SrCl₂. Gel discs were formed by pipetting 2 mLsodium alginate/cell solutions into approximately 10 mL 102 mM SrCl₂ andusing chromatography paper molds (Whatman) immersed in 102 mM CaCl₂respectively. Briefly, to form gel discs, a paper ring with a 2 cmdiameter opening was placed over a 3 cm diameter paper disc. A nylonmesh square with dimension of 1.5 cm×1.5 cm was immersed in 102 mM SrCl₂and then placed in the centre of the paper ring to avoid breakup of gelduring storage. These were saturated with 102 mM SrCl₂ before alginateor alginate/HEC solution (430 μL) containing either hMSC's or mESC'srespectively was pipetted into the space within the ring. A second 3 cmdiameter paper disc saturated with 102 mM SrCl₂ was placed over thealginate/paper assembly. Alginate or alginate/HEC solutions were exposedto 102 mM SrCl₂ for 5 min to allow complete gelation.

The subsequently formed strontium crosslinked alginate discs of 2 cmdiameter containing cells were removed from the paper mold and suspendedin supplemented DMEM medium within a sealed cryo vial. The gels werethen stored at room temperature (18-22° C., atmospheric CO₂) for 5 dayswithout medium change (n>9).

Cryopreservation of mESC and hMSCViable mESC and hMSC were centrifuged at 1500 rpm for 5 mins andfollowed resuspended in freezing medium (50% of mESC or hMSC supplementDMEM, 40% of fresh DMEM and 10% dimethyl sulfoxide (DMSO) (Fisherscientific, U.K.). Each of mESC and hMSC were equally aliquot intocryogenic storage vials (Fisher scientific, U.K.), with finalconcentration of 3×10⁵ cells per vial (n>6). Cryogenic vials weretransferred into Mr. Frosty (Fisher scientific, U.K.) containing of 100ml of isopropyl alcohol (Fisher scientific, U.K.) and placed into −80°C. freezer for overnight to allow cells slowly frozen at 1° C./minute.Finally, Cryogenic vials were transferred into liquid nitrogen for 5days storage.

Nuclear Staining to Analysis of Cell Distribution in HEC-ModifiedStrontium Alginate Gel Discs

hMSC and mESC were encapsulated in strontium alginate (1.2% alginate) orHEC-modified calcium alginate (1.2% alginate/1.2% HEC) gel discs. Gelswere embedded in OCT (TissueTek), frozen and cryosectioned. Transversesections of gels were mounted on glass slides with Vectorshieldcontaining PI fluorescent stain to visualise cell nuclei. Sections wereobserved by fluorescence microscopy (Carl Zeiss Meditec, Germany).

Cell Viability Analysis

Cells were extracted from alginate gel discs by incubation for 4 mins inalginate-dissolving buffer (0.15M NaCl, 0.055M sodium citrate) withgentle agitation. A Trypan blue exclusion assay was performed by mixinga 10 μL of the resulting cell suspension with 10 μL Trypan blue dyesolution (v/v), before counting live (unstained) and dead (stained-blue)cells using a haemocytometer.

Microscopy

Microscopy images were obtained with a Nikon Eclipse TE200-U (Nikon,Japan) colour and fluorescence camera with magnification of 10×.

mESC and hMSC Growth Rate

The mESC and hMSC extracted from alginate after 5 days storage werecultured in supplemented DMEM for approximately 9 days to monitor theability of these cells to attach and form colonies post-extraction andcompare growth rate with cryopreserved cells. Data from individualgrowth curves were used to calculate the doubling time viawww.doubling-time.com.

Isolation of RNA and cDNA Synthesis

Total RNA was isolated using the TRI reagent (Sigma, Poole, U.K.) fromboth mESC and hMSC cells stored either by alginate gel encapsulation orcryopreserved in liquid nitrogen for 5 days according to themanufacturer's protocol. Total RNA was quantified spectrophotometrically(NanoDrop 2000, Thermo scientific, U.K.), and 1 μg RNA wasreverse-transcribed using Revert Aid H Minus First Strand cDNA synthesisKit (Fermentas, U.K.), following the manufacturer's protocol.

Gene Expression Analysis

Expression levels of mouse Oct-4 and SSEA-1, human CD90, CD73 and STRO-1selected genes were determined along with mouse/human GAPDH as areference gene. Primers for all the genes were designed using sequencesobtained from the public domain. RT-PCR was carried out in triplicatewith input of 10 ng cDNA per reaction using Sybr Green Dye (QIAGEN,U.K.) chemistry on the ABI 7900 (Applied Biosystem, U.K.) sequencedetection system. Total reaction volume was 14 μl. Pre-incubation andinitial denaturation of the template cDNA was performed at 95° C. for 10min, followed by amplification for 40 cycles with 95° C. for 15 sec and60° C. for 1 min. The test genes were normalized relative to the mean CTvalue of the reference genes.

Expression levels of the test genes were calculated relative to theirexpression in cells stored in gel. Gene expression calculations weredone using standard and established methods to get the fold change inexpression patterns.

Flow Cytometry Analysis for mESC Markers

The percentage of mESC expressing lineage specific markers wasdetermined using mouse embryonic stem cell multi-colour flow cytometrykit (R&D system, U.K.), according to the manufacturer's protocol. Inbrief, mESC were harvested following four different treatments. 1.Immediately after extraction from alginate gel following 5 days storage;2. Immediately after defrosting following liquid nitrogen storage; 3.After 10 days in standard culture conditions (37° C., 5% CO₂) followingextraction from alginate gels and 4. After 10 days in standard cultureconditions following liquid nitrogen storage followed by 10 daysculturing in incubator. Following each treatment, mESC were washed twiceby PBS in 2% fetal bovine serum, resuspended in 0.5 mL offixation/permeablization buffer and incubated on ice for 30 minutes.Cells were gently vortexed intermittently in order to maintain a singlecell suspension. Cells were then centrifuged, and the cell pelletresuspended in 200 μl of the permeabilization/wash buffer, at whichpoint 10 μl of Sox2-PE, Oct3/4-APC, SSEA-1-PerCP, SSEA-4-FL1 antibodiesor each corresponding isotype control antibody was added to the cells,and then incubated for 30-45 minutes on ice in the dark. Following theincubation, excess antibody was removed by washing the cells in 2 mlpermeabilization/wash buffer; the final cell pellet was resuspended in400 μl of PBS for flow cytometric analysis. Flow cytometry was performedusing BD FACSCanto II cytometer (BD bioscience, USA).

Statistical Analysis

Unpaired Student's t-tests were performed using Microsoft Excel. QPCRand flow cytometry results are presented as the mean of 3 individualexperiments with standard error of mean and P-value 0.05 consideredsignificant.

Results Cell Encapsulated Inside Aliginate Gel

The composite gel, comprised of an alginate gel for cell encapsulationcontaining a nylon mesh, showed increased mechanical properties (FIG.12).

Cell density and distribution of hMSC and mESC following encapsulationwithin the alginate-nylon gels were shown to be similar, both showing aneven distribution throughout the gel FIG. 13.

The Survival Status of hMSC and mESC Inside Strontium Alginate Gel Discs

To examine the suitability of a strontium alginate gel disc forpreservation and storage of hMSC and mESC, the proportion of viablecells retrieved following encapsulation and storage were investigated.

After a 5-day storage period, the proportion of live cells retrievedfollowing alginate encapsulation or cryopreservation were comparedbetween hMSC and mESC (FIG. 14 and FIG. 15). The number of viable hMSCretrieved from alginate gel discs (82.22%) was slightly higher thanthose retrieved following cryopreservation (77.78%); in contrast, mESCstored inside alginate gel did not maintain the same level of viability(44.44%), the number retrieved following cryopreservation was similar tohMSC (74%) (FIG. 14).

In terms of the proportion of relative cell survival (i.e. not includingcells that have been lost during the storage process) the two differentstorage conditions for both hMSC and mESC provided a similar level.Approximately 80% of the retrieved hMSC from alginate-nylon gels wereviable, 5% lower than the cryopreserved hMSC. However, mESC storedinside alginate gel discs actually showed increased proportion ofinitial encapsulated cells (74%) than cryopreserved mESC (69%) (FIG.15).

Survival Status of hMSC and mESC Post-Extraction

To further evaluate the cells' growth following extraction fromstrontium alginate-nylon gel storage, cell-doubling assays wereperformed on the extracted hMSC and mESC. Post-extracted culture of bothhMSC and mESC at 37° C. under 5% CO₂ and 95% humidity demonstrated thatcells from alginate gel discs were still capable of assembling intocolonies (FIG. 16). More importantly, extracted cells not only survived,but also maintained similar proliferation rates. Cell doublingmeasurements clearly showed no significant difference between untreatedcultured cells and those extracted from calcium alginate gel discs (FIG.17) using the same passage number and initial seeding density.

Expression of Common Cell Markers Following Extraction from StrontiumAlginate-Nylon Gels after 5 Days Storage.

To validate the cells phenotype after storage within strontium alginategel at room temperature, a number of robust stem cell markers wereexamined. Quantitative PCR analyses were performed on hMSC and mESCbefore and after 5 days in storage within either alginate gel discs orcryopreservation. Both mesenchymal and embryonic cell markers wereexamined respectively. The QPCR results showed no sign of decreasinglevels of common hMSC and mESC stem cell markers (FIG. 18 and FIG. 19).Interestingly, mRNA levels of both hMSC (CD90, CD73 and STRO-1) and mESCmarkers (Oct-4 and SSEA-1) actually increased after 5 days storage bothinside alginate gels and in liquid nitrogen (cryopreservation). mRNAlevels of hMSC markers from cells stored inside alginate gels were veryclose to cells stored in liquid nitrogen. Surprisingly, for mESC storedinside alginate gel, both Oct-4 and SSEA-1 mRNA levels were two foldhigher than from cryopreserved mESC. Flow cytometry was performedagainst four specific mESC markers following either storage for 5 days(in either alginate gel or liquid nitrogen) or 10 days incubation at 37°C. under 5% CO₂ and 95% humidity (of previously cryo- or gel-storedcells). Following storage, expression of OCT 3/4 and SSEA4 wassignificantly decreased by cryo-preservation but following 10 days inoptimal culture conditions they increased to levels similar to thoseseen in the alginate encapsulated cells. Interestingly the expression ofeach marker remained stable following gel encapsulation, suggestingcells could be used immediately following release from the gel (FIG.20).

Example 10 Storage of Different Cell Types

A number of different cell types were stored in a 1.2% alginate gel discat ambient conditions for 5 days. The results showed high viabilitylevels after storage across a range of different cell types includingimmortalised cell lines, primary cells lines and stem cells (FIG. 21).

1. (canceled)
 2. A method for preparing cells for transportation from afirst location to a second location, the method comprising the steps:(i) encapsulating or entrapping the cells in a hydrogel, wherein thehydrogel is a 1.1-1.3% strontium alginate hydrogel, wherein the hydrogelis in the form of a thin layer or disc; and (iia) packaging thecell-containing hydrogel for transportation from the first location tothe second location; and/or (iib) dispatching the cell-containinghydrogel for transportation from the first location to the secondlocation. 3.-11. (canceled)
 12. The method, as claimed in claim 2,wherein the hydrogel is obtained or obtainable using a pore sizeincreasing agent.
 13. The method, as claimed in claim 12, wherein thepore size increasing agent produces pores the range 0.1-3.0 μm,preferably 0.2-3.0 μm, 0.1-1.0 μm or 0.1-0.4 μm.
 14. The method, asclaimed in claim 12, wherein the pore size increasing agent is a watersoluble polymer, preferably HEC.
 15. The method, as claimed in claim 2,wherein the cells entrapped or encapsulated within the hydrogel aremammalian cells, preferably human cells.
 16. The method, as claimed inclaim 2, wherein the cells entrapped or encapsulated within the hydrogelcomprise neural cells or stem cells, preferably corneal stem cells,mesenchymal stem cells or embryonic stem cells.
 17. The method, asclaimed in claim 2, wherein cell division and/or cell differentiation ofall or a substantial proportion of the cells which are entrapped orencapsulated within the hydrogel is suppressed or prevented. 18.-20.(canceled)
 21. The method, as claimed in claim 2, wherein the hydrogelis stored during a transportation step or otherwise under cell cultureconditions, ambient conditions or chilled conditions, or is frozen priorto transportation or storage.
 22. The method, as claimed in claim 2,wherein the cells are retained in the hydrogel during a transportationstep or otherwise for 1-10 days or 1-10 weeks before being released fromthe hydrogel.
 23. A process for the preparation of a hydrogel comprisingliving cells, the process comprising the steps: (i) gelling ahydrogel-forming polymer in the presence of living cells and awater-soluble pore size increasing agent; and (ii) dissolving all or asubstantial proportion of the pore size increasing agent out of thehydrogel.
 24. A process as claimed in claim 23, wherein the pore sizeincreasing agent is HEC. 25.-29. (canceled)
 30. A hydrogel comprisingliving cells, wherein the hydrogel is a 0.5%-1.3%, preferably about 0.6%or about 1.2%, calcium or strontium alginate hydrogel in the form of athin layer or disc, preferably with a thickness of 0.1-5.0 mm.
 31. Ahydrogel as claimed in claim 30, wherein hydrogel comprises detectablelevels of the water-soluble pore size increasing agent; and wherein thehydrogel is obtained by or obtainable by a process, comprising: (i)gelling a hydrogel-forming polymer in the presence of living cells and awater-soluble pore size increasing agent; and (ii) dissolving all or asubstantial proportion of the pore size increasing agent out of thehydrogel.
 32. A method of treating a wound or an illness caused by awound in a subject, the method comprising contacting the wound with ahydrogel as defined in claim
 30. 33. (canceled)
 34. (canceled)
 35. Amethod of aiding blood clotting in a subject which is bleeding, themethod comprising contacting the site of bleeding with a hydrogel asdefined in claim
 30. 36. (canceled)
 37. (canceled)
 38. A method oftreating an ocular injury in a subject, the method comprising the steps:(a) providing a hydrogel comprising corneal stem cells, wherein thecells are provided by a method as claimed in claim 2; (b) contacting theocular injury with said hydrogel; and optionally (c) securing the saidhydrogel at the site of the ocular injury.
 39. A method of treating asubject having a damaged ocular surface, the method comprising thesteps: (a) providing a hydrogel comprising corneal stem cells and/orgrowth factors secreted or secretable by corneal stem cells, wherein thecells are provided by a method as claimed in claim 2; (b) optionallyremoving diseased cells and/or tissue from the damaged ocular surface ofthe subject; (c) contacting the damaged ocular surface with saidhydrogel; and (d) optionally securing the said hydrogel at the site ofthe damaged ocular surface.
 40. A method of treating a damaged ocularsurface in a subject, the method comprising the steps: (a) providing ahydrogel comprising corneal stem cells and/or growth factors secreted orsecretable by corneal stem cells, wherein the cells are provided by amethod as claimed in claim 2; (b) optionally removing diseased cellsand/or tissue from the damaged ocular surface of the subject; (c)contacting the damaged ocular surface with said hydrogel; and (d)optionally securing the said hydrogel at the site of the damaged ocularsurface. 41.-46. (canceled)
 47. A composition comprising a hydrogel, asclaimed in claim 30, wherein a population of cells is encapsulated orentrapped within the hydrogel, wherein the hydrogel is a 1.1-1.3%strontium alginate hydrogel, wherein the hydrogel is in the form of athin layer or disc, and wherein the composition is packaged in a formsuitable for transportation to a remote location.